Methods and apparatus for pressure therapy in the treatment of sleep disordered breathing

ABSTRACT

A controller or processor for a respiratory pressure treatment device determines an estimate of patient respiratory flow based on a measure of pressure associated with flow generated by a flow generator and a measure of frequency of the flow generator, such as a rotational velocity of a servo-controlled blower motor. The estimate can be made without data from a flow sensor. The measure of frequency may be converted to an expected pressure based on characteristics of the flow generator and subtracted from the measured pressure to determine the flow estimate. The flow estimate can be implemented in the provision of respiratory pressure treatment with the flow generator. For example, the flow estimate may be utilized to trigger expiratory pressure relief during a patient&#39;s expiration as detected with the estimated flow signal.

CROSS REFERENCE TO RELATED APPLICATIONS

This application claims the benefit of the filing dates of U.S.Provisional Patent Application Nos. 60/965,171 filed Aug. 17, 2007 and61/125,066 filed Apr. 22, 2008, the disclosures of which are herebyincorporated herein by reference.

FIELD OF THE TECHNOLOGY

The present technology relates to methods and apparatus for treatment ofrespiratory conditions such as the conditions related to obstructivesleep apnea hypopnea syndrome (OSAHS) or obstructive sleep apnea (OSA).

BACKGROUND OF THE TECHNOLOGY

Patients with OSA have recurrent apnoeas or hypopnoeas during sleep thatare only terminated by the patient arousing. These recurrent eventscause sleep fragmentation and stimulation of the sympathetic nervoussystem. This can have severe consequences for the patient includingday-time sleepiness (with the attendant possibility of motor-vehicleaccidents), poor mentation, memory problems, depression andhypertension. Patients with OSA are also likely to snore loudly, thusalso disturbing their partner's sleep. The best form of treatment forpatients with OSA is constant positive airway pressure (CPAP) applied bya blower (compressor) via a connecting hose and mask (patientinterface). The positive pressure prevents collapse of the patient'sairway during inspiration, thus preventing recurrent apnoeas orhypopnoeas and their sequelae.

Positive airway pressure may be delivered in many forms. For example, apositive pressure level may be maintained across the inspiratory andexpiratory levels of the patient's breathing cycle at an approximatelyconstant level. Alternatively, pressure levels may be adjusted to changesynchronously with the patient's breathing cycle. For example, pressuremay be set at one level during inspiration and another lower levelduring expiration for patient comfort. Such a pressure treatment systemmay be referred to as bi-level. Alternatively, the pressure levels maybe continuously adjusted to smoothly replicate changes in the patient'sbreathing cycle. A lower pressure setting during expiration maygenerally be referred to as expiratory pressure relief.

In providing such changes to pressure and/or detecting conditions formaking adjustments to the treatment pressure, it can be helpful to havea measure of patient respiratory flow. For example, a measure of patientrespiratory flow may be utilized to detect when a patient changes frominspiration to expiration for determining when to deliver expiratorypressure treatment settings or inspiratory pressure treatment settings.Similarly, a measured patient respiratory flow signal may be utilized todetect patient flow limitation for purposes of making treatment pressureadjustments. Such adjustments are illustrated in the patent in U.S. Pat.No. 5,704,345. For these purposes, a measured flow signal may be derivedfrom a flow sensor such as a differential pressure transducer orpnuemotachograph.

It may be desirable to develop further methods and devices forestimating flow to improve existing methods and devices and/or todevelop new pressure treatment and detection methods and devices.

SUMMARY OF THE TECHNOLOGY

Aspects of the present technology involve methods for a respiratory flowgenerating apparatus. In one method, a measure of pressure produced by arespiratory flow generating apparatus and a measure of a frequency ofthe respiratory flow generating apparatus are determined. The methodthen derives an estimate of patient respiratory flow as a function ofthe measure of pressure and the measure of frequency. In someembodiments, the measure of frequency may be a rotational velocity.Moreover, the deriving of the estimate may further include determiningan expected pressure as a function of the measure of frequency and mayfurther include calculating a difference between the determined expectedpressure and the measure of pressure. Pressure treatment by therespiratory flow generating apparatus may be set or adjusted as afunction of the derived estimate of respiratory flow.

In one embodiment, the technology encompasses an apparatus forgenerating respiratory flow. The apparatus may optionally include apatient interface to carry a flow of breathable gas to a patient. Theapparatus may further include a flow generator coupled with the patientinterface to generate a flow of the breathable gas through the patientinterface. The apparatus may also include measurement sensors such as apressure transducer to provide a pressure signal indicative of pressurein a portion of the patient interface or associated with the flowgenerator and a tachometer to provide a velocity signal indicative of aspeed of the flow generator. The apparatus may also be provided with acontroller to control the flow generator. The controller is coupled withthe pressure transducer to process the pressure signal and it is coupledwith the tachometer to process the velocity signal. The controller maybe configured and adapted to control a method for estimating patientrespiratory flow or to set delivered treatment pressure by a method asdescribed herein such as by determining a measure of pressure with thepressure signal, determining a measure of frequency with the velocitysignal and deriving an estimate of patient respiratory flow as afunction of the measure of pressure and the measure of frequency.

In a further embodiment, a system for delivering respiratory flow to apatient includes an interface means to carry a flow of breathable gas.The system may also include a flow means, coupled with the interfacemeans, for generating the breathable gas. The system may have a pressuresensing means for measuring pressure and for generating a pressuresignal representing the measured pressure of the breathable gas as wellas a frequency sensing means for measuring a frequency of the flow meansand for generating a frequency signal representing the measuredfrequency. The system will typically also include a processing means forprocessing the pressure signal and the frequency signal. The processingmeans may be configured or adapted for processing a determination of ameasure of pressure with the pressure signal, a determination of ameasure of frequency with the frequency signal and a derivation of anestimate of patient respiratory flow as a function of the measure ofpressure and the measure of frequency. The processing means may also beconfigured for controlling a generation of pressure with the flow meansas a function of the derived estimate of respiratory flow. In anembodiment of the system, changes to pressure treatment may be deliveredin synchrony with a patient's respiratory cycle without a flow sensor orutilizing a signal from a flow sensor.

In another embodiment, methodology of the technology may be encoded onan information-bearing medium as software or firmware. For example, aninformation-bearing medium may include processor-readable information orprocessor control instructions. The processor-readable information maycontrol an apparatus for providing pressure treatment therapy. Theprocessor-readable information or processor control instructions mayinclude steps that implement determining a measure of pressure producedby a flow generator, determining a measure of frequency of the flowgenerator and deriving an estimate of patient respiratory flow as afunction of the measure of pressure and the measure of frequency.

Further embodiments and features of the technology will be apparent fromthe following detailed disclosure, claims and drawings.

BRIEF DESCRIPTION OF DRAWINGS

The present technology is illustrated by way of example, and not by wayof limitation, in the figures of the accompanying drawings, in whichlike reference numerals refer to similar elements including:

FIG. 1 shows example components of an apparatus for respiratory flowestimation and pressure treatment based thereon;

FIG. 2 is a flow chart for a method for a pressure treatment or flowestimation apparatus of the present technology;

FIG. 3 is an illustrative input/output diagram for a control circuit orprocessor implementing flow estimation technology;

FIG. 4 is a graph of an exemplary pressure treatment waveformimplemented by a pressure treatment apparatus utilizing the present flowestimation technology;

FIG. 5 is a diagram illustrating suitable components of a feedbackcontrol loop of a pressure treatment device utilizing flow estimationtechnology for mask swing adjustment.

DETAILED DESCRIPTION

In reference to FIG. 1, the present technology may be implemented with apressure treatment delivery device that may include a flow generatorsuch as a servo-controlled blower 102. The blower 102 will typicallyinclude an air inlet and impeller driven by a motor (not shown).

In the embodiment illustrated in FIG. 1, a frequency sensor 104 isprovided. The sensor may be configured to measure the rotationalvelocity of the blower. For example, a tachometer may measure therevolutions per minute (RPM) of the blower's motor or the blower'simpeller. The frequency sensor 104 may be configured to generate afrequency signal f(t) indicative of the measurements of the sensor.

The device of FIG. 1 may further include a pressure sensor 106, such asa pressure transducer. The pressure sensor 106 is configured to measurethe pressure generated by the blower 102. In this embodiment, thepressure sensor 106 is proximate to the blower 102 but may be locateddownstream of the blower as desired. The pressure sensor 106 generates apressure signal p(t) indicative of the measurements of pressure. Thepressure sensor 106 and frequency sensor 104 have only been shownsymbolically in FIG. 1 since it is understood that other configurationsand other components may be implemented to measure the frequency andpressure associated with the blower 102.

The pressure treatment delivery device will also typically include apatient interface such as an air delivery conduit 108 and a mask 110 tocarry a flow of air or breathable gas to and/or from a patient. Theblower 102 can be coupled with the air delivery conduit 108 and the mask110 so as to provide the breathable gas from the blower 102. Exhaust gascan be vented from the patient interface via an exhaust 111.

The frequency f(t) and pressure p(t) signals may be sent to a controlleror processor 112. Optional analog-to-digital (A/D) converters/samplers(not shown separately) may be utilized in the event that suppliedsignals from the frequency and pressure sensors are not in digital formand the controller is a digital controller. Based on input signals fromthese sensors and/or other optional sensors, the controller may in turngenerate blower control signals. For example, the controller maygenerate an RPM request signal to control the speed of the blower 102 bysetting a desired frequency or rotational velocity set point andcomparing it with the measured condition of the frequency sensor.Alternatively, such changes may be based on determining a desiredpressure set point and comparing it with the measured condition of thepressure sensor. Typically, such changes to the motor speed areaccomplished by increasing or decreasing supplied motor current with theservo based on determined differences between set and measuredconditions such as in a closed loop feedback fashion and translating thedifference to current. Thus, the processor 112 or controller may makecontrolled changes to the pressure delivered to the patient interface bythe blower 102. Optionally, such changes to pressure may be implementedby controlling the exhaust with a mechanical release valve (not shown)to increase or decrease the exhaust while maintaining a relativelyconstant blower speed.

The controller or processor 112 is typically configured and adapted toimplement particular control methodology such as the methods describedin more detail herein. Thus, the controller may include integratedchips, a memory and/or other control instruction, data or informationstorage medium. For example, programmed instructions encompassing such acontrol methodology may be coded on integrated chips in the memory ofthe device or such instructions may be loaded as software or firmwareusing an appropriate medium. With such a controller or processor, theapparatus can be used for many different pressure treatment therapies,such as the pressure treatments previously mentioned, by adjusting apressure delivery equation that is used to set the speed or pressure ofthe blower or the exhaust venting by the release valve.

For example, based on such a configuration, an embodiment of the systemmay determine or estimate a patient respiratory flow, even without aflow signal from a flow sensor, and then adjust the pressure treatmentdelivered by the device based on patient respiratory conditions detectedfrom or with the estimated flow signal. While the flow characteristicsof the hose to the mask may also impact pressure determinations, such aflow estimation model can be based on the premise that in anrpm-controlled system the load perturbations (i.e., patient respiratoryflow) are reflected in the pressure output of the device. Similarly, ina pressure-controlled system the load perturbations will be reflected inthe rpm output of the device.

Thus, in one embodiment, two measures, such as pressure and flowgenerator system frequency (e.g., a rotational velocity of the blowersuch as RPM) taken together can give a measure of flow. In one suitablepatient flow estimate, the measured pressure and an expected pressurevalue derived from the frequency measure may both be utilized to derivethe flow as a function thereof. This can be illustrated with thefollowing function:

Flow=function (P_(M)−P_(RPM) _(_) _(derived))

Where:

-   -   P_(M) is a measured pressure;    -   P_(RPM) _(_) _(derived) is an expected pressure at a particular        flow that is determined or calculated from a measured system        variable other than pressure such as frequency or rotational        velocity (e.g., RPM) of the blower. Depending on the flow        generator characteristics and required accuracy, it can also be        either a fixed value or calibrated value.

In one embodiment, P_(RPM) _(_) _(derived) may be determined orcalculated by a static fan curve as follows:

P _(RPM-derived) =K ₂*ω² +K ₁ +K ₀

Where:

-   -   ω is an angular frequency of the flow generator (which may also        be referred to as angular speed, radial frequency, and radian        frequency); and    -   K₂, K₁ and K₀ may be experimentally pre-determined constants for        relating an experimental measure of delivered pressure to a        blower's measured angular frequency based on the particular        structural characteristics of the flow generator or blower        (e.g., impeller design). Optionally, in the case of small        constants, the constants may be uniformly scaled up to reduce        operational overhead of decimal point operations on a device's        processor or controller.

In one embodiment, the flow may then be determined as a function of thedifference between P_(M) and P_(RPM) _(_) _(derived) by utilizing thefollowing equation:

Flow=A ₃ *x ³ A ₂ * x ² +A ₁ *x+A ₀

Where:

-   -   x is P_(M) minus P_(RPM-derived) as previously described; and    -   A₃, A₂, A₁ and A₀ may be experimentally pre-determined constants        for relating an experimental measure of flow to a function of        the blower's measured angular frequency and measured pressure        based on the particular structural characteristics of the        system.

However, given the limitations of 32-bit processing, it was found thatthe computational complexity was quite high for arriving at the desiredlevel of performance of flow linearization using the above equation.Thus, in another embodiment of the technology, in order to simplify thedetermination, a look up table may be pre-formed based on the aboveequations. A suitable table may be pre-calculated based on a range ofinput measures of frequency and a range of input measures of pressureusing the formulas. The output of the table would then be a derivedinstantaneous flow value based on an input instantaneous measure ofpressure and an input instantaneous measure of frequency as previouslydescribed.

In a still further embodiment of the technology, the derived flow valuesmay be determined from the difference between the measured pressure andthe frequency derived pressure (e.g., P_(M)—P_(RPM) _(_) _(derived)).Thus, the flow may be more simply estimated by the following equation:

Flow=P _(M) −P _(RPM) _(_) _(derived)

Where:

-   -   P_(M) is a measured pressure; and    -   P_(RPM) _(_) _(derived) is an expected pressure that is        determined or calculated from a measured system variable other        than pressure such as frequency or rotational velocity (e.g.,        RPM or ω) of the blower by any method previously discussed.

Although this particular estimate is not linearized, it can give anestimate of flow excursion. Therefore, it is quite suitable foralgorithms that are dependent on cycle detection. In the absence offurther processing, it may not alone be highly suitable for algorithmsthat require more accurate flow value or more accurate flow shape.However, its simplicity can make it particularly suitable forimplementation either as a hardware component to reduce a systemprocessor load or as firmware/software for a system processor.

In a system that employs a continuous system exhaust flow or leak withwhich the patient respiratory flow is combined, the above determinedflow values may be further processed to separate the system or leak flowfrom the patient respiratory flow by a suitable operation such as oneillustrated by the following equation:

Respiratory Flow=FLW−LPF(FLW)

Where:

-   -   FLW is continuously or periodically determined flow values        derived from any of the previously described methods; and    -   LPF(FLW) is a low pass filtering operation on the flow values        with the filtering operation being chosen to remove a constant        component of the flow that can be associated with a relatively        constant leak or system flow. An example operation may be low        pass filtering with a time constant of 10 seconds.

FIG. 3 illustrates the flow estimate methodology with respect to acontroller or processor 312. A measured pressure value signal 302 (p(t))and a measured frequency value signal 304 (ω(t)) are input to a flowestimate algorithm 306 for deriving an estimated flow value signal 308.The flow estimate algorithm 306 is based on any of the calculations orfunctions as previously discussed such as one or more flow lookup tables330.

An estimate of flow (e.g., estimated patient respiratory flow) made byany of the methods discussed herein may then be used in any suitableflow-based determinations typically made by a pressure treatment device.For example, the derived flow estimate can be used to make a change inpressure upon detection of features of the patient respiratory cycle. Inan illustrative embodiment, the derived flow estimate may be used totrigger an expiratory pressure relief. In such an embodiment, aratiometric trigger threshold, such as a trigger threshold that is afunction of the peak respiratory flow, may be utilized to detect theonset of expiration. Utilizing such a trigger in particular combinationwith any of the above estimates of flow that might deviate marginallyfrom actual patient flow provides for a more reliable or resilientrespiratory cycle detection and appropriate pressure response.

In this embodiment, the technology can be implemented according to thefollowing pseudo code:

-   -   if (RespiratoryFlow>PeakRespiratoryFlow/Y) or (EPR has been on        for over 15 sec) then Turn EPR off    -   else if (RespiratoryFlow<0) then Turn EPR on

Where:

-   -   RespiratoryFlow is a derived flow estimate made by any of the        methods previously described;    -   PeakRespiratoryFlow is a pre-peak respiratory flow value, such        as a peak determined in a prior respiratory cycle;    -   Y is some divisor of the peak respiratory flow (e.g., 4); and    -   EPR is a procedure that implements a reduction in the delivered        treatment pressure setting for patient comfort.

In this embodiment, a bi-level pressure treatment therapy may begenerated such that a reduced pressure level is delivered by the EPRduring patient expiration and a higher treatment pressure level withoutthe EPR reduction is delivered during patient inspiration. Depending onthe flow generator characteristics or settings, such as a motor falltime and rise time, the changes between an inspiratory level and anexpiratory level may be gradual such that a smoother pressure changebetween the inspiratory pressure treatment levels and the expiratorypressure treatments may be effected.

An example pressure waveform that may be delivered in accordance withthe present technology is illustrated in the graph of FIG. 4. FIG. 4includes a plot of a patient simulation flow waveform 402 that has beengenerated by a patient flow simulation apparatus. The patient flowsimulation apparatus was coupled with the patient interface of apressure treatment device that implements flow estimation technologydescribed herein. FIG. 4 also includes a graph of a pressure waveform404 generated using the flow estimation and triggering technologydiscussed herein within the pressure treatment device. The graphillustrates that the device may deliver pressure adjustment in synchronywith the cycle of the patient simulation flow waveform 402 based on theestimated flow methodology.

A pressure treatment device can be affected by changes to pressure inthe system introduced by the patient's respiratory cycle. In the eventthat the sensors utilized for control of pressure levels to the mask ofthe patient interface are located proximate to the flow generator,rather than the mask of the patient interface, undesirable swings inmask pressure can be induced by the patient's respiration. Theseundesirable mask pressure swings can be adjusted with the controller tomaintain more steady pressure levels by utilizing the present estimatedpatient flow technology.

For example, in another embodiment, the pressure treatment devicecontrols pressure rather than controlling motor rpm and a pressuresensor used for the control is located at or proximate to the flowgenerator. In the embodiment, the measure of pressure that will be usedin the feedback loop for pressure control is adjusted as a function ofthe estimate of flow. This adjustment is implemented in a predictivemanner in an effort to impede mask swings induced by the patient'srespiratory cycle. For example, the measured control pressure may beadjusted according to the following method:

MeasuredPressure_(adjusted)=MeasuredPressure−FlowFactor

Where:

-   -   FlowFactor is a function of an estimate of flow determined by        any of the previously described methods.

In one embodiment, this function of the estimate of flow may bemultiplying the estimate by a value K, where K is a value that isdifferent for positive flow (e.g., patient inspiration) and than fornegative flow (e.g., patient expiration). The value for K may beexperimentally chosen for positive and negative flow as desired toidentify optimum values for swing reduction that generate more steadymask pressure in response to patient respiration.

The adjusted measure of pressure may then be applied to a pressurecontrol feedback loop such as a control loop implementing PseudoDerivative Feedback (PDF) control as follows:

Error=DesiredPressure−MeasuredPressure_(adjusted)

MotorCommand=P*Error+I∫Error

Where:

-   -   DesiredPressure is a determined treatment pressure setting such        as an inspiratory or expiratory treatment pressure level;    -   MeasuredPressure_(adjusted) is the adjusted pressure as        previously described;    -   P and I are factors chosen for translation of the pressure        setting to an adjustment of the current applied to the motor of        the flow generator for adjusting a particular motor's speed        based on the characteristics of the motor.

Controller components of such swing compensation control are illustratedin FIG. 5. An estimated flow value or signal is supplied to a measuredpressure adjustor 550 along with a pressure value or signal measured bya pressure sensor 556. A pressure setting value or signal is supplied tothe servo 552 along with an adjusted measured pressure value or signal.Based on these signals, the servo adjusts the motor current forcontrolling the output or speed of the motor 554 of the flow generatorto thereby adjust the pressure delivered by the flow generator device topredictively reduce mask pressure swings induced by patient respiration.

In a still further embodiment, swing compensation control may beimplemented with a modified version of the swing control equation. Insuch an embodiment, the pressure at the flow generator is controlled bycomparing a desired pressure set point with the measurement from thepressure sensor. In other words, the flow generator may be controlled sothat a pressure set point is equal to a measure of pressure determinedfrom a pressure sensor at the flow generator.

However, because the pressure at the flow generator is controlled to theset point, the pressure fluctuations at the mask are a result of theflow related pressure drop through the patient interface or deliverycircuit. This may be represented by the following equation:

MaskPres=PresSetPoint−PresLossInDeliveryCircuit

Where:

-   -   MaskPres is the pressure in the patient mask or patient        interface,    -   PresSetPoint is a desired pressure or target pressure,    -   PresLosslnDeliveryCircuit is a pressure loss due to the        impedance of the delivery circuit.

Pressure fluctuations in the mask can be reduced by modifying themeasured pressure as previously described as follows:

MeasuredPressure_(adjusted) =P _(M)−FlowFactor

where

-   -   P_(M) is a measure of pressure from a sensor such as a pressure        transducer.        The FlowFactor may represent the pressure drop in the delivery        circuit and can be assumed to be proportional to an estimate of        flow. For example,

FlowFactor=ImpedOfDeliveryCir*Flow

where

-   -   ImpedOfDeliveryCir is the impedance of the delivery circuit or        patient interface,    -   Flow is an estimate of flow as previously determined.

However, since the estimate of flow may be considered to be a functionof the pressure drop across the flow generator as previously described,then the pressure drop can be approximated to be proportional to theestimate of flow according to the following equation:

Flow=PresDropAcrossTurbine/ImpedanceOfTurbine;

-   -   where    -   PresDropAcrossTurbine is a pressure drop across the flow        generator such as one determined as a difference between a        measured pressure and a derived pressure as previously described        (e.g., P_(M)−P_(RPM) _(_) _(derived)), and    -   ImpedanceofTurbine is an impedance of the flow generator which        may depend on the particular design of the flow generator and        may be predetermined and/or preset into the memory of the        controller of the system.

By combining the preceding flow factor equation with this immediatelypreceding flow equation, an explicit computation of one of thepreviously described estimates of flow need not be made for swingcompensation. Rather, the determination may be implicitly implementedwhen considering the following:

FlowFactor=PresDropAcrossTurbine*ImpedOfDeliveryCir/ImpedanceOfTurbine

By applying this FlowFactor to the equation for the adjusted measure ofpressure, a further expression may be obtained for the adjustment inmeasured pressure as follows:

MeasuredPressure_(Adjusted) =P _(M) −K*PressureDropAcrossTurbine

where

-   -   K is a ratio of two impedances such as ImpedOfDeliveryCircuit        divided by the ImpedanceOfTurbine.

Such an equation may then be implemented for swing compensation controlin a pressure treatment delivery device of the present technology bycontrolling the respiratory treatment apparatus to generate pressure sothat the adjusted measure of pressure meets a target or desired pressuresetting.

In the foregoing description and in the accompanying drawings, specificterminology, equations and drawing symbols are set forth to provide athorough understanding of the present technology. In some instances, theterminology and symbols may imply specific details that are not requiredto practice the technology. Moreover, although the technology herein hasbeen described with reference to particular embodiments, it is to beunderstood that these embodiments are merely illustrative of theprinciples and applications of the technology. It is therefore to beunderstood that numerous modifications may be made to the illustrativeembodiments and that other arrangements may be devised without departingfrom the spirit and scope of the technology.

For example, the flow estimate technology may be implemented in a systemutilized for detecting patient flow limitation or making otheradjustments to the delivered treatment pressure of a pressure treatmentdevice. Moreover, the flow estimate may be utilized in systems having aflow sensor. In such a system, the flow estimate technology describedherein may serve as back up flow determination in the event of failureof a flow sensor that is used for flow based determinations.Alternatively, the estimate of flow data may be combined with data froma flow sensor to generate combined flow data to insulate the system frommore transient errors in either the flow signal from the flow sensor orthe derived estimate of flow described herein.

1-34. (canceled)
 35. A method of controlling pressure in a pressuretreatment delivery apparatus to compensate for patient induced swing ata patient interface, the method comprising: determining a measure ofpressure delivered by a flow generator with a pressure sensor, thepressure sensor being located proximate to the flow generator; adjustingthe measure of pressure as a function of (a) a measure of pressure dropacross the flow generator, (b) a measure of impedance of a patientinterface coupled to the flow generator and (c) a measure of impedanceof the flow generator; and controlling the flow generator so that theadjusted measure of pressure satisfies a target pressure setting. 36.The method of claim 35 wherein the function multiplies the measure ofpressure drop with a ratio of the measure of impedance of the patientinterface and the measure of impedance of the flow generator.
 37. Themethod of claim 36 wherein a result of the function is subtracted fromthe measure of pressure.
 38. The method of claim 37 wherein the measureof pressure drop is a difference between a measure of pressure and aderived measure of pressure that is a determined function of a frequencyof the flow generator.
 39. A pressure treatment delivery apparatus tocompensate for patient induced swing comprising: a patient interface tocarry a flow of breathable gas to a patient; a flow generator coupledwith the patient interface to generate a flow of the breathable gasthrough the patient interface; a pressure sensor to provide a pressuresignal indicative of pressure associated with the flow generator; and aprocessor to control the flow generator, the processor coupled with thepressure sensor to process the pressure signal, the processor beingconfigured to control: determining a measure of pressure delivered by aflow generator with the pressure sensor, the pressure sensor beinglocated proximate to the flow generator; adjusting the measure ofpressure as a function of (a) a measure of pressure drop across the flowgenerator, (b) a measure of impedance of a patient interface and (c) ameasure of impedance of the flow generator; and controlling the flowgenerator so that the adjusted measure of pressure satisfies a targetpressure setting.
 40. The apparatus of claim 39 wherein the functionmultiplies the measure of pressure drop with a ratio of the measure ofimpedance of the patient interface and the measure of impedance of theflow generator.
 41. The apparatus of claim 40 wherein a result of thefunction is subtracted from the measure of pressure.
 42. The apparatusof claim 41 wherein the measure of pressure drop is a difference betweena measure of pressure and a derived measure of pressure that is adetermined function of a frequency of the flow generator.
 43. A pressuretreatment delivery system to compensate for patient induced swingcomprising: a patient interface means for carrying a flow of breathablegas to a patient; a flow generation means coupled with the patientinterface for generating a flow of the breathable gas through thepatient interface; a sensor means for providing a pressure signalindicative of pressure associated with the flow generator; and a controlmeans, coupled with the sensor means and flow generation means, fordetermining a measure of pressure delivered by the flow generationmeans, for adjusting the measure of pressure as a function of (a) ameasure of pressure drop across the flow generator, (b) a measure ofimpedance of a patient interface and (c) a measure of impedance of theflow generator, and for controlling the flow generator so that theadjusted measure of pressure satisfies a target pressure setting. 44.The system of claim 43 wherein the function multiples the measure ofpressure drop with a ratio of the measure of impedance of the patientinterface and the measure of impedance of the flow generator.
 45. Thesystem of claim 44 wherein a result of the function is subtracted fromthe measure of pressure.
 46. The system of claim 45 wherein the measureof pressure drop is a difference between a measure of pressure and aderived measure of pressure that is a determined function of a frequencyof the flow generator.
 47. An information-bearing medium havingprocessor-readable information thereon, the processor-readableinformation to control an apparatus for providing pressure treatmenttherapy to compensate for patient induced swing, the processor-readableinformation comprising control instructions to: determine a measure ofpressure delivered by a flow generator with a pressure sensor that islocated proximate to the flow generator; adjust the measure of pressureas a function of (a) a measure of pressure drop across the flowgenerator, (b) a measure of impedance of a patient interface coupled tothe flow generator and (c) a measure of impedance of the flow generator;and control the flow generator so that the adjusted measure of pressuresatisfies a target pressure setting.
 48. The medium of claim 47 whereinthe function multiplies the measure of pressure drop with a ratio of themeasure of impedance of the patient interface and the measure ofimpedance of the flow generator.
 49. The medium of claim 48 wherein aresult of the function is subtracted from the measure of pressure. 50.The medium of claim 47 wherein the measure of pressure drop is adifference between a measure of pressure and a derived measure ofpressure that is a determined function of a frequency of the flowgenerator.